WO2004010733A1 - Hearing aid system and hearing aid method - Google Patents

Hearing aid system and hearing aid method Download PDF

Info

Publication number
WO2004010733A1
WO2004010733A1 PCT/JP2003/002361 JP0302361W WO2004010733A1 WO 2004010733 A1 WO2004010733 A1 WO 2004010733A1 JP 0302361 W JP0302361 W JP 0302361W WO 2004010733 A1 WO2004010733 A1 WO 2004010733A1
Authority
WO
WIPO (PCT)
Prior art keywords
coil
magnetic field
hearing aid
vibrating
eardrum
Prior art date
Application number
PCT/JP2003/002361
Other languages
French (fr)
Japanese (ja)
Inventor
Hiroshi Wada
Takuji Koike
Toshimitsu Kobayashi
Original Assignee
Tohoku University
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Tohoku University filed Critical Tohoku University
Priority to CA002469676A priority Critical patent/CA2469676A1/en
Publication of WO2004010733A1 publication Critical patent/WO2004010733A1/en
Priority to US10/863,295 priority patent/US20040234092A1/en

Links

Classifications

    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/60—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles
    • H04R25/604—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers
    • H04R25/606—Mounting or interconnection of hearing aid parts, e.g. inside tips, housings or to ossicles of acoustic or vibrational transducers acting directly on the eardrum, the ossicles or the skull, e.g. mastoid, tooth, maxillary or mandibular bone, or mechanically stimulating the cochlea, e.g. at the oval window
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R25/00—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception
    • H04R25/55—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired
    • H04R25/554—Deaf-aid sets, i.e. electro-acoustic or electro-mechanical hearing aids; Electric tinnitus maskers providing an auditory perception using an external connection, either wireless or wired using a wireless connection, e.g. between microphone and amplifier or using Tcoils
    • H—ELECTRICITY
    • H04—ELECTRIC COMMUNICATION TECHNIQUE
    • H04R—LOUDSPEAKERS, MICROPHONES, GRAMOPHONE PICK-UPS OR LIKE ACOUSTIC ELECTROMECHANICAL TRANSDUCERS; DEAF-AID SETS; PUBLIC ADDRESS SYSTEMS
    • H04R2225/00—Details of deaf aids covered by H04R25/00, not provided for in any of its subgroups
    • H04R2225/023—Completely in the canal [CIC] hearing aids

Definitions

  • the present invention relates to a hearing aid system and a hearing aid method for vibrating a vibration coil placed on an eardrum using an electromagnetic coil.
  • Hearing aids are devices that collect and amplify sound to make it easier for people with hearing loss.
  • Currently used hearing aids can be broadly divided into two types.
  • One is the earphone-type hearing aid that is widely used. This type of hearing aid is placed in the outer ear area, amplifies and outputs external sound, and vibrates the eardrum by the vibration of air. Examples of the form include a portable earphone radio type, an earphone type, and an earplug-insertable type such as an earplug.
  • the other is an artificial middle ear type hearing aid in which a vibrator such as a piezo element or a permanent magnet is directly attached to the ossicle and driven.
  • This type of hearing aid is not affected by the acoustic properties of the ear canal and can provide high quality sound.
  • each type of hearing aid has the following problems.
  • earphone-type hearing aids are placed in the ear canal with a narrow and complex shape, it is difficult to achieve accurate sound pressure amplification characteristics up to the high frequency range. That is, if the path through which the sound is transmitted has a tubular and complex shape, such as the ear canal, resonance or interference occurs. Subordinate Thus, hearing through hearing aids is different from natural sounds.
  • the artificial middle ear type hearing aid requires "invasion" of the human body, such as removing a part of the skull and removing the ossicles of the middle ear when attaching the transducer. Therefore, the mental and physical burden on the user is large.
  • the present invention has been made in view of the above circumstances, and an object of the present invention is to provide a hearing aid system and a hearing aid method that can realize accurate sound pressure amplification characteristics even in a high sound range and do not require invasion of the human body.
  • a first aspect of the present invention is a hearing aid system provided from the outer ear region to the eardrum, wherein the current generator generates a current based on an input external sound, and the time of a magnetic field is determined based on the current.
  • a first coil for inducing a temporal change a second coil for generating an induced electromotive force based on the temporal change of the magnetic field, a magnetic field generator provided to face the eardrum, and the second coil.
  • a vibration coil that vibrates the eardrum by vibrating itself due to interaction with a magnetic field.
  • the vibration coil is adhered to a surface of the eardrum on the outer ear region side using oil or a clip. It is.
  • the third viewpoint of the present invention relates to a hearing aid system according to the first viewpoint.
  • the parts that come into contact with the human body are covered with a biocompatible, indispensable material.
  • the magnetic field generator is arranged in an outer ear region near a middle ear region.
  • the vibration coil has a weight of 2 Omg or less.
  • a sixth aspect of the present invention is the hearing aid system according to the first aspect, wherein the vibration coil has a disk shape.
  • the strength of the induced magnetic field can be adjusted by controlling a distance between the magnetic field generator and the vibration coil. It is something that is.
  • the magnetic field generator is a permanent magnet.
  • an AC current is generated based on the external sound input from a sound input means provided in an outer ear region, and the AC current is caused to flow through a first coil.
  • Inducing a temporal change in the magnetic field generating an induced electromotive force in the second coil based on the temporal change in the magnetic field, and applying an induced magnetic field, whose polarity changes based on the induced electromotive force, to the eardrum
  • the vibrating coil is caused to vibrate by vibrating the vibrating coil by a magnetostatic field generated by a magnet provided to face the eardrum and an induced magnetic field generated by the vibrating coil.
  • a hearing aid method is there.
  • a tenth viewpoint of the present invention is the hearing aid method according to the ninth viewpoint, wherein the vibration coil is provided on a surface of the eardrum on the outer ear region side by using a foil or a clip. It is what is glued.
  • a portion in contact with a human body is covered with a biocompatible insulating material.
  • the magnet is disposed in an outer ear region near a middle ear region.
  • a thirteenth viewpoint of the present invention relates to a ninth viewpoint.
  • the vibrating coil weighs not more than 2 Omg.
  • a fourteenth aspect of the present invention is the capture method according to the ninth aspect, wherein the vibrating coil has a disk shape.
  • the intensity of the induction magnetic field can be adjusted by controlling a distance between the magnet and the vibration coil. It is something that is.
  • FIG. 1 is a diagram for explaining a schematic configuration of a hearing aid system according to the present embodiment.
  • FIG. 2 is a diagram for explaining a schematic configuration of the hearing aid system according to the present embodiment.
  • Fig. 3 shows the results when the vibrating coils 21 with different masses were placed on the eardrum and a vibration force equivalent to a sound pressure of 80 d BSPL was applied.
  • 6 is a graph showing the relationship between frequency and cochlear sound pressure.
  • FIGS. 1 and 2 are diagrams for explaining a schematic configuration of the hearing aid system according to the present embodiment.
  • the hearing aid system has a microphone 11, an amplifier 13, a primary coil 15, a secondary coil 17, a permanent magnet 19, and a vibrating coil 21.
  • Microphone 1 receives external sounds such as conversation sounds and converts them into electrical signals.
  • the amplifier 13 amplifies the electric signal converted by the microphone 11 to a predetermined intensity level.
  • the amplification intensity can be controlled to any level. ⁇
  • the electric signal amplified by the amplifier 13 flows through the primary coil 15. Therefore, the primary coil 15 generates an induced magnetic field in response to a change in the electric signal based on the voice.
  • the secondary coil 17 generates an induced electromotive force based on a change in the magnetic field caused by the primary coil 15.
  • the shape of the secondary coil 17 is not particularly limited, in the present embodiment, the primary coil 17 is used in order to increase the density of magnetic flux penetrating the secondary coil 17 and efficiently generate an induced electromotive force. It is a shape that surrounds.
  • the permanent magnet 19 is supported by a predetermined frame and Fixed on the road. As described later, the static magnetic field generated by the permanent magnet 19 serves as a drive source for vibrating the vibrating coil 21. In order to make this vibration efficient and to prevent displacement due to contact with human fingers, the permanent magnet 19 faces the vibrating coil 21 and is as close to the eardrum as possible (ie, It is preferable to be installed in the ear canal as close to the middle ear as possible.
  • the vibration coil 21 is a lightweight coil that is adhered to the eardrum surface on the ear canal side using oil. According to the experiments by the inventors, if the weight is, for example, 20 mg or less, the inertia can be sufficiently suppressed, and a sound close to a natural sound can be provided (see FIG. 3). .
  • a clip made of a shape memory alloy may be attached to the vibrating coil 21 so that a part of the ossicle is sandwiched between the eardrum surface of the ear canal and the clip.
  • the shape of the vibration coil 21 is not particularly limited. However, in order to generate a larger exciting force by strengthening the magnetic field inside the vibrating coil 21, to cause microvibration at high speed, and to stabilize it dynamically, it must be disc-shaped. Is preferred.
  • portions that may come into contact with the skin are covered with a biocompatible material in order to prevent inflammation.
  • a portion through which a current flows is covered with a current leakage preventing material in order to prevent a current from leaking into a living tissue.
  • a material that satisfies these two conditions is, for example, silicon.
  • the amplified electric signal is supplied to the primary coil 15 as an alternating current.
  • an alternating current flows through the primary coil 15
  • the magnetic field around the primary coil 15 changes with time, and changes the magnetic flux passing through the secondary coil 17.
  • an induced electromotive force is generated in the secondary coil 17 in proportion to the temporal change of the magnetic field.
  • the current generated by the induced electromotive force generated in the secondary coil 17 is supplied to the vibration coil 21 electrically connected to the secondary coil 17. 'When a current due to the induced electromotive force flows through the vibrating coil 21, an induced magnetic field due to the induced electromotive force is generated around the vibrating coil 21. Due to the interaction between the induction magnetic field and the static magnetic field formed by the permanent magnet 19, a driving force for exciting the eardrum is generated in the vibration coil 21.
  • the sound input to the microphone 11 includes the AC current supplied to the primary coil 15, the induced electromotive force generated in the secondary coil 17, and the induced magnetic field generated by the induced electromotive force.
  • the permanent magnet 19 Via the interaction of the permanent magnet 19 with the magnetostatic field, it is transmitted to the vibrating coil 21 provided on the eardrum surface as an exciting force.
  • external voice can be transmitted to the eardrum as vibration, and functions as a hearing aid.
  • This hearing aid system 10 uses a lightweight vibration coil 21. Therefore, since the inertia of the vibration coil 21 is small, even when external sound of a high frequency band is input, vibration can be efficiently reduced. It can be transmitted to the eardrum.
  • Figure 3 shows the results when the vibrating coils 21 (20 mg, 40 mg, 100 mg) of different masses were placed on the tympanic membrane and a vibration force equivalent to a sound pressure of 80 d BSPL was applied.
  • 6 is a graph showing the relationship between frequency and cochlear sound pressure. As shown in the figure, by reducing the weight of the vibrating coil 21, it is possible to obtain a sound pressure close to the normal state (the thick solid line in the figure) without the vibrating coil 21. it can.
  • the hearing aid system 10 has a configuration in which a lightweight vibration coil 21 is bonded with oil or the like, and a microphone 11 or a permanent magnet 19 is installed from the outer ear region to the eardrum. Therefore, it can be easily mounted without any invasive surgery on the human body. As a result, it can be used casually by young and old people in their growing stages.
  • Conventional earphone-type hearing aids amplify the sound input to the microphone and transmit the amplified sound directly to the eardrum.
  • resonance or interference of the sound waves may occur in the ear canal having a narrow and complicated shape.
  • the sound through the hearing aid may not faithfully reproduce the natural sound.
  • conventional earphone-type hearing aids since the distance between the earphone and the microphone is short, the sound output from the power of the earphone may be input again by the microphone, resulting in howling.
  • the hearing aid system 10 vibrates the vibrating coil 21 provided on the eardrum surface by magnetic interaction using electromagnetic induction. This causes the eardrum to vibrate. Therefore, phenomena such as resonance and interference of acoustic waves, howling and the like do not occur as in the related art, and there is no acoustic restriction. As a result, natural sound can be faithfully reproduced with high sound quality.
  • the hearing aid system 10 amplifies the electric signal converted from the input voice, generates magnetic interaction using electromagnetic induction based on the amplified electric signal,
  • the vibrating coil 21 provided at the point is excited. Therefore, by controlling the amplification degree of the electric signal, the distance between the vibrating coil 21 and the permanent magnet 19, and the like. A larger magnetic interaction is generated, and a driving force for vibrating the vibrating coil 21 can be obtained. Because of these characteristics and being free from the acoustic restrictions described above, it is possible to provide clear hearing aid even for a highly mixed hearing loss patient.
  • the present hearing system 10 is a simple and low-cost device, it will provide many people with good communication in the aging society expected in the future. And can be.
  • each embodiment may be implemented in combination as appropriate as possible, and in such a case, the combined effect can be obtained.
  • the above embodiments include inventions at various stages, and various inventions can be made by appropriately combining a plurality of disclosed constituent elements. Can be extracted. For example, even if some components are deleted from all the components shown in the embodiment, the problem described in the problem to be solved by the invention can be solved, and the problem described in the effect of the invention can be solved. If at least one of the above effects can be obtained, a configuration from which this configuration requirement has been deleted can be extracted as an invention.
  • an accurate sound pressure amplification characteristic can be realized even in a high sound range, and a hearing aid system and a hearing aid method that do not require invasion of the human body can be realized.

Abstract

A voice inputted in a microphone (11) is converted into an electrical signal and amplified by an amplifier (13). The amplified electrical signal is supplied to a primary coil (15) as an alternating current. Thus, the peripheral magnetic field of the primary coil (15) changes with time, so that an induced electromotive force develops in a secondary coil (17). A vibrating coil (21) is supplied with a current caused by the induced electromotive force, so that an induced magnetic field is produced around the vibrating coil (21). The vibrating coil (21) provided on an eardrum face is excited by the interaction of this induced magnetic field and a static magnetic field generated by a permanent magnet (19).

Description

明 細 書  Specification
捕聴シス テ ム及び補聴方法  Hearing system and hearing aid
技術分野 Technical field
本発明は、 電磁コイルを用いて、 鼓膜面に留置された振動 コ イ ルを振動させる補聴シス テ ム及び補聴方法に関する。  The present invention relates to a hearing aid system and a hearing aid method for vibrating a vibration coil placed on an eardrum using an electromagnetic coil.
背景技術 Background art
補聴器と は、 難聴の人のために、 音を集めた り 増幅したり して聞こえやすく するための装置である。 現在使用されてい る補聴器は大き く 二つのタイプに分ける こ とができる。 一つ は、 一般に普及 しているイヤホンタイ プの補聴器である。 こ のタイプの補聴器は、 外耳領域に配置され、 外部音声を増幅 して出力 し、 空気の振動によ り鼓膜を振動させる ものである。 その形態と しては、 例えば携帯型イヤホンラジオ型のもの， 耳かけ型のもの， 耳栓のよ う に外耳道への挿入型のもの等が める。  Hearing aids are devices that collect and amplify sound to make it easier for people with hearing loss. Currently used hearing aids can be broadly divided into two types. One is the earphone-type hearing aid that is widely used. This type of hearing aid is placed in the outer ear area, amplifies and outputs external sound, and vibrates the eardrum by the vibration of air. Examples of the form include a portable earphone radio type, an earphone type, and an earplug-insertable type such as an earplug.
も う一つは、 ピエゾ素子や永久磁石等の振動子を直接耳小 骨に取り 付けて駆動させる人工中耳タイプの補聴器である。 このタイプの補聴器は、 外耳道の音響特性の影響を受けない から、 質の高い音を提供する こ とができ る。  The other is an artificial middle ear type hearing aid in which a vibrator such as a piezo element or a permanent magnet is directly attached to the ossicle and driven. This type of hearing aid is not affected by the acoustic properties of the ear canal and can provide high quality sound.
しかしながら、 各タイプの補聴器には、 それぞれ以下に述 ベる問題がある。  However, each type of hearing aid has the following problems.
イヤホンタイ プの補聴器は、 狭く 複雑な形状の外耳道に配 置されるため、 高音域まで正確な音圧増幅特性を実現するの は困難である。 すなわち、 音が伝わる経路が、 外耳道の如く 管状で複雑な形状を している場合、 共振や干渉が生じる。 従 つて、 補聴器を通した聞こえ方は、 自然音と違って しま う。 また、 人工中耳タイ プの補聴器は、 振動子を取り付ける際 に頭蓋骨の一部を削 り 取る， 中耳の耳小骨を取り 除く 等、 人 体への "侵襲" を必要とする。 従って、 使用者への精神的、 肉体的な負担は大きい。 Since earphone-type hearing aids are placed in the ear canal with a narrow and complex shape, it is difficult to achieve accurate sound pressure amplification characteristics up to the high frequency range. That is, if the path through which the sound is transmitted has a tubular and complex shape, such as the ear canal, resonance or interference occurs. Subordinate Thus, hearing through hearing aids is different from natural sounds. In addition, the artificial middle ear type hearing aid requires "invasion" of the human body, such as removing a part of the skull and removing the ossicles of the middle ear when attaching the transducer. Therefore, the mental and physical burden on the user is large.
発明の開示 Disclosure of the invention
本発明は、 上記事情を鑑みてなされたもので、 高音域であ つても正確な音圧増幅特性を実現でき、 人体への侵襲を必要 と しない補聴システム及び補聴方法を提供する こ と を目的と している。  The present invention has been made in view of the above circumstances, and an object of the present invention is to provide a hearing aid system and a hearing aid method that can realize accurate sound pressure amplification characteristics even in a high sound range and do not require invasion of the human body. And
本発明の第 1 の視点は、 外耳領域から鼓膜にかけて設け ら れる補聴システムであって、 入力 した外部音声に基づいて電 流を発生する電流発生器と、 前記電流に基づいて、 磁場の時 間的変化を誘導する第 1 のコイルと、 前記磁場の時間的変化 に基づいて、 誘導起電力を発生する第 2 のコイルと、 前記鼓 膜に対向 して設け られる磁場発生器と、 前記第 2 のコイルと 電気的に接続され、 かつ前記鼓膜に設けられる コイルであつ て、 前記誘導起電力に基づいて極性が変化する磁場を発生し、 当該極性が変化する磁場と前記磁場発生器が発生する磁場と の相互作用によ り 自身が振動する こ とで前記鼓膜を振動させ る振動コィルと、 を具備する補聴システムである。  A first aspect of the present invention is a hearing aid system provided from the outer ear region to the eardrum, wherein the current generator generates a current based on an input external sound, and the time of a magnetic field is determined based on the current. A first coil for inducing a temporal change, a second coil for generating an induced electromotive force based on the temporal change of the magnetic field, a magnetic field generator provided to face the eardrum, and the second coil. A coil that is electrically connected to the coil and is provided on the eardrum, and generates a magnetic field whose polarity changes based on the induced electromotive force, and generates the magnetic field whose polarity changes and the magnetic field generator. And a vibration coil that vibrates the eardrum by vibrating itself due to interaction with a magnetic field.
本発明の第 2 の視点は、 第 1 の視点に係る補聴システムに おいて、 前記振動コイルは、 前記鼓膜の外耳領域側の面に、 オイル又はク リ ップを用いて接着されている ものである。  According to a second aspect of the present invention, in the hearing aid system according to the first aspect, the vibration coil is adhered to a surface of the eardrum on the outer ear region side using oil or a clip. It is.
本発明の第 3 の視点は、 第 1 の視点に係る補聴システムに おいて、 人体と の接触部分については、 生体適合性のある絶 緣素材にて被覆されている ものである。 The third viewpoint of the present invention relates to a hearing aid system according to the first viewpoint. In this case, the parts that come into contact with the human body are covered with a biocompatible, indispensable material.
本発明の第 4 の視点は、 第 1 の視点に係る補聴システムに おいて、 前記磁場発生器は、 中耳領域寄り の外耳領域に配置 されている ものである。  According to a fourth aspect of the present invention, in the hearing aid system according to the first aspect, the magnetic field generator is arranged in an outer ear region near a middle ear region.
本発明の第 5 の視点は、 第 1 の視点に係る補聴システムに おいて、 前記振動コイルは、 2 O m g以下の重量である もの である。  According to a fifth aspect of the present invention, in the hearing aid system according to the first aspect, the vibration coil has a weight of 2 Omg or less.
本発明の第 6 の視点は、 第 1 の視点に係る補聴システムに おいて、 前記振動コイルは、 円盤形である ものである。  A sixth aspect of the present invention is the hearing aid system according to the first aspect, wherein the vibration coil has a disk shape.
本発明の第 7 の視点は、 第 1 の視点に係る補聴システムに おいて、 前記磁場発生器と前記振動コイルと の間の距離を制 御する こ と で、 前記誘導磁場の強度を調整可能である もので あ 。  According to a seventh aspect of the present invention, in the hearing aid system according to the first aspect, the strength of the induced magnetic field can be adjusted by controlling a distance between the magnetic field generator and the vibration coil. It is something that is.
本発明の第 8 の視点は、 第 1 の視点に係る補聴システムに おいて、 前記磁場発生器は、 永久磁石である ものである。  According to an eighth aspect of the present invention, in the hearing aid system according to the first aspect, the magnetic field generator is a permanent magnet.
本発明の第 9 の視点は、 外耳領域に設け られた音声入力手 段から入力 した前記外部音声に基づいて交流電流を発生させ、 前記交流電流を第 1 のコイルに流すこ と によ って、 磁場の時 間的変化を誘導し、 前記磁場の時間的変化に基づいて、 第 2 のコイルに誘導起電力を発生させ、 前記誘導起電力に基づい て極性が変化する誘導磁場を、 鼓膜に設け られた振動コイル に発生させ、 前記鼓膜に対向 して設け られた磁石による静磁 場と、 前記振動コイルが発生する誘導磁場によ り 、 前記振動 コイルを振動させる こ とで前記鼓膜を振動させる補聴方法で ある。 According to a ninth aspect of the present invention, an AC current is generated based on the external sound input from a sound input means provided in an outer ear region, and the AC current is caused to flow through a first coil. Inducing a temporal change in the magnetic field, generating an induced electromotive force in the second coil based on the temporal change in the magnetic field, and applying an induced magnetic field, whose polarity changes based on the induced electromotive force, to the eardrum The vibrating coil is caused to vibrate by vibrating the vibrating coil by a magnetostatic field generated by a magnet provided to face the eardrum and an induced magnetic field generated by the vibrating coil. In a hearing aid method is there.
本発明の第 1 0 の視点は、 第 9 の視点に係る補聴方法にお いて、 前記振動コ イ ルは、 前記鼓膜の外耳領域側の面に、 ォ ィル又はク リ ップを用いて接着されている ものである。  A tenth viewpoint of the present invention is the hearing aid method according to the ninth viewpoint, wherein the vibration coil is provided on a surface of the eardrum on the outer ear region side by using a foil or a clip. It is what is glued.
本発明の第 1 1 の視点は、 第 9 の視点に係る補聴方法にお いて、 人体と の接触部分については、 生体適合性のある絶縁 素材にて被覆されている ものであ る。  According to a eleventh aspect of the present invention, in the hearing aid method according to the ninth aspect, a portion in contact with a human body is covered with a biocompatible insulating material.
本発明の第 1 2 の視点は、 第 9 の視点に係る補聴方法にお いて、 前記磁石は、 中耳領域寄り の外耳領域に配置されてい る ものであ る。  According to a twelfth aspect of the present invention, in the hearing aid method according to the ninth aspect, the magnet is disposed in an outer ear region near a middle ear region.
本発明.の第 1 3 の視点は、 第 9 の視点に係る.捕聴方法にお いて、 前記振動コイルは、 2 O m g以下の重量である もので ある。  A thirteenth viewpoint of the present invention relates to a ninth viewpoint. In the listening method, the vibrating coil weighs not more than 2 Omg.
本発明の第 1 4の視点は、 第 9 の視点に係る捕聰方法にお いて、 前記振動コ イ ルは、 円盤形である ものである。  A fourteenth aspect of the present invention is the capture method according to the ninth aspect, wherein the vibrating coil has a disk shape.
本発明の第 1 5 の視点は、 第 9 の視点に係る補聴方法にお いて、 前記磁石と前記振動コ イ ル と の間の距離を制御する こ と で、 前記誘導磁場の強度を調整可能である ものである。 図面の簡単な説明  According to a fifteenth aspect of the present invention, in the hearing aid method according to the ninth aspect, the intensity of the induction magnetic field can be adjusted by controlling a distance between the magnet and the vibration coil. It is something that is. BRIEF DESCRIPTION OF THE FIGURES
図 1 は、 本実施形態に係る補聴シス テム の概略構成を説明 するための図である。  FIG. 1 is a diagram for explaining a schematic configuration of a hearing aid system according to the present embodiment.
図 2 は、 本実施形態に係る補聴シス テム の概略構成を説明 するための図である。  FIG. 2 is a diagram for explaining a schematic configuration of the hearing aid system according to the present embodiment.
図 3 は、 異なる質量の各振動コイル 2 1 を鼓膜面に留置し て音圧 8 0 d B S P L相当の加振力を加えた場合における、 周波数と蝸牛内音圧と の関係を示したグラフである。 Fig. 3 shows the results when the vibrating coils 21 with different masses were placed on the eardrum and a vibration force equivalent to a sound pressure of 80 d BSPL was applied. 6 is a graph showing the relationship between frequency and cochlear sound pressure.
発明を実施するための最良の形態 BEST MODE FOR CARRYING OUT THE INVENTION
以下、 本発明の実施形態を図面に従って説明する。 なお、 以下の説明において、 略同一の機能及び構成を有する構成要 素については、 同一符号を付し、 重複説明は必要な場合にの み行 う。  Hereinafter, embodiments of the present invention will be described with reference to the drawings. In the following description, components having substantially the same functions and configurations are denoted by the same reference numerals, and repeated description will be made only when necessary.
図 1 及び図 2 は、 本実施形態に係る補聴システムの概略構 成を説明するための図である。 図 1及び図 2 に示す様に、 本 補聴システムは、 マイ ク 1 1 、 アンプ 1 3 、 一次コイル 1 5 、 二次コイ ル 1 7、 永久磁石 1 9 、 振動コイル 2 1 を有してい る  1 and 2 are diagrams for explaining a schematic configuration of the hearing aid system according to the present embodiment. As shown in FIGS. 1 and 2, the hearing aid system has a microphone 11, an amplifier 13, a primary coil 15, a secondary coil 17, a permanent magnet 19, and a vibrating coil 21.
マイ ク 1 は、 会話音等の外界の音声を受信し、 電気信号 に変換する。  Microphone 1 receives external sounds such as conversation sounds and converts them into electrical signals.
ア ンプ 1 3 は、 マイ ク 1 1 によって変換された電気信号を 所定の強度レベルに増幅する。 なお、 この増幅強度は、 任意 の レベルに制御可能である。 ·  The amplifier 13 amplifies the electric signal converted by the microphone 11 to a predetermined intensity level. The amplification intensity can be controlled to any level. ·
一次コイル 1 5 には、 アンプ 1 3 によって増幅された電気 信号が流れる。 従って、 当該一次コイル 1 5 は、 音声に基づ く 電気信号の変化に応 じて誘導磁場を発生する。  The electric signal amplified by the amplifier 13 flows through the primary coil 15. Therefore, the primary coil 15 generates an induced magnetic field in response to a change in the electric signal based on the voice.
二次コイル 1 7 は、 一次コイル 1 5 が引き起こす磁場の変 化に基づいて、 誘導起電力を発生する。 この二次コイル 1 7 の形状には特に限定はないが、 本実施形態では、 二次コィル 1 7 を貫く 磁束の密度を多く し効率的に誘導起電力を発生さ せるため、 一次コイル 1 5 を包囲する形状と なっている。  The secondary coil 17 generates an induced electromotive force based on a change in the magnetic field caused by the primary coil 15. Although the shape of the secondary coil 17 is not particularly limited, in the present embodiment, the primary coil 17 is used in order to increase the density of magnetic flux penetrating the secondary coil 17 and efficiently generate an induced electromotive force. It is a shape that surrounds.
永久磁石 1 9 は、 所定のフ レームによって支持され、 外耳 道に固定される。 後述する様に、 本永久磁石 1 9 が発生する 静磁場は、 振動コイ ル 2 1 を振動させる駆動源と なる。 この 振動を効率的にするため、 及び人の指等と の接触による位置 ずれを防止するために、 当該永久磁石 1 9 は、 振動コイル 2 1 に直面し、 でき る限り鼓膜寄り （すなわち、 でき る限り 中 耳寄り の外耳道） に設け られる こ とが好ま しい。 The permanent magnet 19 is supported by a predetermined frame and Fixed on the road. As described later, the static magnetic field generated by the permanent magnet 19 serves as a drive source for vibrating the vibrating coil 21. In order to make this vibration efficient and to prevent displacement due to contact with human fingers, the permanent magnet 19 faces the vibrating coil 21 and is as close to the eardrum as possible (ie, It is preferable to be installed in the ear canal as close to the middle ear as possible.
振動コイル 2 1 は、 外耳道側の鼓膜面に、 オイルを用いて 接着される軽量なコイルである。 発明者らの実験によれば、 . その重さは例えば 2 0 m g 以下であれば慣性を十分に抑える こ とができ、 自然音に近い聞こえを提供する こ と ができ る （図 3 参照） 。 また、 振動コイル 2 1 は、 形状記憶合金で作った ク リ ップを取り付けて， 外耳道側の鼓膜面から耳小骨の一部 をク リ ップで挟み込むこ とでもよい。  The vibration coil 21 is a lightweight coil that is adhered to the eardrum surface on the ear canal side using oil. According to the experiments by the inventors, if the weight is, for example, 20 mg or less, the inertia can be sufficiently suppressed, and a sound close to a natural sound can be provided (see FIG. 3). . In addition, a clip made of a shape memory alloy may be attached to the vibrating coil 21 so that a part of the ossicle is sandwiched between the eardrum surface of the ear canal and the clip.
この振動コイル 2 1 の形状については特に限定はない。 し かしながら、 当該振動コイル 2 1 内部の磁界を強く してよ り 大きな加振力を生み出すため、 高速に微少振動させるため、 動力学的に安定にするために、 円盤形である こ と が好ま しい。  The shape of the vibration coil 21 is not particularly limited. However, in order to generate a larger exciting force by strengthening the magnetic field inside the vibrating coil 21, to cause microvibration at high speed, and to stabilize it dynamically, it must be disc-shaped. Is preferred.
なお、 以上述べた各構成要素において、 皮膚に接触する可 能性のある部分については、 炎症を防止するため、 生体適合 性材料によって被覆されている こ とが好ま しい。 また、 電流 が流れる部分については、 生体組織への電流漏れを防止する ため、 電流漏洩防止材によ って被覆する こ と が好ま しい。 こ の二つの条件を満足する材料と しては、 例えばシリ コ ンがあ る。  In each of the above-described components, it is preferable that portions that may come into contact with the skin are covered with a biocompatible material in order to prevent inflammation. In addition, it is preferable that a portion through which a current flows is covered with a current leakage preventing material in order to prevent a current from leaking into a living tissue. A material that satisfies these two conditions is, for example, silicon.
次に、 本捕聴システムの動作原理について説明する。 図 2 において、 マイ ク 1 1 が外界の音声を受信する と、 当 該音声は電気信号に変換され、 アンプ 1 3 によ り 所定の強度 レベルま で増幅される 。 · Next, the operating principle of the present listening system will be described. In FIG. 2, when the microphone 11 receives an external sound, the sound is converted into an electric signal and amplified by the amplifier 13 to a predetermined intensity level. ·
増幅された電気信号は、 交流電流と して一次コ イ ル 1 5 に 供給される。 一次コ イ ル 1 5 に交流電流が流れる と、 当該一 次コ イル 1 5 の周 り の磁場が時間的に変化 し、 二次コ イ ル 1 7 を貫く 磁束を変化させる。 その結果、 二次コイル 1 7 には、 当該磁場の時間的変化に比例する誘導起電力が発生する。  The amplified electric signal is supplied to the primary coil 15 as an alternating current. When an alternating current flows through the primary coil 15, the magnetic field around the primary coil 15 changes with time, and changes the magnetic flux passing through the secondary coil 17. As a result, an induced electromotive force is generated in the secondary coil 17 in proportion to the temporal change of the magnetic field.
二次コ イ ル 1 7 と電気的に接続されている振動コ イ ル 2 1 には、 二次コ イ ル 1 7 に発生した誘導起電力によ る電流が供 給される。' 振動コ イ ル 2 1 に誘導起電力によ る電流が流れる と、 当該振動コ イ ル 2 1 の周 り には、 こ の誘導起電力に起因 する誘導磁場が発生する。 こ の誘導磁場と永久磁石 1 9 が形 成する静磁場と の相互作用によ り 、 振動コ イ ル 2 1 には、 鼓 膜を加振する駆動力が発生する。  The current generated by the induced electromotive force generated in the secondary coil 17 is supplied to the vibration coil 21 electrically connected to the secondary coil 17. 'When a current due to the induced electromotive force flows through the vibrating coil 21, an induced magnetic field due to the induced electromotive force is generated around the vibrating coil 21. Due to the interaction between the induction magnetic field and the static magnetic field formed by the permanent magnet 19, a driving force for exciting the eardrum is generated in the vibration coil 21.
すなわち、 マイ ク 1 1 に入力される音声は、 一次コ イ ル 1 5 に供給される交流電流、 二次コ イ ル 1 7 に発生する誘導起 電力、 当該誘導起電力によ る誘導磁場と永久磁石 1 9 の静磁 場と の相互作用を介 して、 加振力 と して鼓膜面に設け られた 振動コイル 2 1 に伝え られる。 これによ り 、 外部音声を振動 と して鼓膜に伝える こ とができ、 補聴器と して機能する。  That is, the sound input to the microphone 11 includes the AC current supplied to the primary coil 15, the induced electromotive force generated in the secondary coil 17, and the induced magnetic field generated by the induced electromotive force. Via the interaction of the permanent magnet 19 with the magnetostatic field, it is transmitted to the vibrating coil 21 provided on the eardrum surface as an exciting force. As a result, external voice can be transmitted to the eardrum as vibration, and functions as a hearing aid.
こ の よ う な構成によれば、 以下の効果を得る こ とが出来る。 本補聴システ ム 1 0 は、 軽量な振動コ イ ル 2 1 を使用 して いる。 従って、 振動コ イ ル 2 1 の慣性が小さいため、 高周波 数帯の外部音声を入力 した場合であっても、 振動を効率よ く 鼓膜面に伝える こ と ができ る。 According to such a configuration, the following effects can be obtained. This hearing aid system 10 uses a lightweight vibration coil 21. Therefore, since the inertia of the vibration coil 21 is small, even when external sound of a high frequency band is input, vibration can be efficiently reduced. It can be transmitted to the eardrum.
図 3 は、 異なる質量の各振動コイル 2 1 ( 2 0 m g 、 4 0 m g 、 1 0 0 m g ) を鼓膜面に留置して音圧 8 0 d B S P L 相当の加振力を加えた場合における、 周波数と蝸牛内音圧と の関係を示 したグラフである。 同図に示すよ う に、 振動コィ ル 2 1 を軽量化する こ とで、 振動コイル 2 1 を留置していな い通常時 （図中 「太い実線」 ） に近い音圧を得る こ とができ る。  Figure 3 shows the results when the vibrating coils 21 (20 mg, 40 mg, 100 mg) of different masses were placed on the tympanic membrane and a vibration force equivalent to a sound pressure of 80 d BSPL was applied. 6 is a graph showing the relationship between frequency and cochlear sound pressure. As shown in the figure, by reducing the weight of the vibrating coil 21, it is possible to obtain a sound pressure close to the normal state (the thick solid line in the figure) without the vibrating coil 21. it can.
本補聴システム 1 0 は、 軽量な振動コイル 2 1 をオイル等 で接着し、 また、 外耳領域から鼓膜にかけてマイ ク 1 1 や永 久磁石 1 9 等を設置する構成と なっている。 従って、 人体へ の侵襲手術を全く 必要とせず、 容易に装着する こ とができ る。 その結果、 成長段階にある幼児から老人まで、 気軽に利用す る こ とができ る。  The hearing aid system 10 has a configuration in which a lightweight vibration coil 21 is bonded with oil or the like, and a microphone 11 or a permanent magnet 19 is installed from the outer ear region to the eardrum. Therefore, it can be easily mounted without any invasive surgery on the human body. As a result, it can be used casually by young and old people in their growing stages.
従来のイヤホン型の補聴器は、 マイ ク に入力された音を増 幅し、 その増幅された音を直接鼓膜に伝える ものである。 こ のよ う に音波によ り 直接鼓膜を振動させる構成では、 狭く 複 雑な形状を した外耳道において、 音波の共振や干渉が発生す る こ とがある。 その結果、 補聴器を介 した音声が、 自然音声 を忠実に再現しない場合がある。 また、 従来のイヤホン型の 補聴器は、 イヤホンとマイ ク の距離が近いため、 イヤホン力 ら出力された音を再びマイ クが入力 して しまい、 ハウ リ ング を発生する こ と がある。  Conventional earphone-type hearing aids amplify the sound input to the microphone and transmit the amplified sound directly to the eardrum. In such a configuration in which the tympanic membrane is vibrated directly by the sound waves, resonance or interference of the sound waves may occur in the ear canal having a narrow and complicated shape. As a result, the sound through the hearing aid may not faithfully reproduce the natural sound. Also, in conventional earphone-type hearing aids, since the distance between the earphone and the microphone is short, the sound output from the power of the earphone may be input again by the microphone, resulting in howling.
これに対し、 本補聴システム 1 0 は、 電磁誘導を利用 した 磁気相互作用によ り 、 鼓膜面に設けた振動コイル 2 1 を加振 させる こ と で鼓膜を振動させる。 従って、 従来のよ う に音波 の共振及ぴ干渉、 ハウ リ ング等の現象そのものが発生せず、 音響学的制約を受けない。 その結果、 自然音声を高い音質に て忠実に再現する こ とができ る。 In contrast, the hearing aid system 10 vibrates the vibrating coil 21 provided on the eardrum surface by magnetic interaction using electromagnetic induction. This causes the eardrum to vibrate. Therefore, phenomena such as resonance and interference of acoustic waves, howling and the like do not occur as in the related art, and there is no acoustic restriction. As a result, natural sound can be faithfully reproduced with high sound quality.
また、 本補聴シス テ ム 1 0 は、 入力 した音声から変換され た電気信号を増幅し、. 当該増幅された電気信号に基づいて、 ， 電磁誘導を利用 した磁気相互作用を発生させ、 鼓膜面に設け た振動コイル 2 1 を加振させる。 従って、 電気信号の増幅度 や、 振動コイル 2 1 と永久磁石 1 9 と の距離等を制御する こ とで。 よ り 大きな磁気相互作用を発生させ、 振動コイル 2 1 を振動させ.る駆動力を得る こ と ができ る。 こ の様な特性や、 上記音響学的制約を受けないこ と から、 高度混合性難聴者に 対しても、 明瞭な補聴を提供する こ とができ る。  In addition, the hearing aid system 10 amplifies the electric signal converted from the input voice, generates magnetic interaction using electromagnetic induction based on the amplified electric signal, The vibrating coil 21 provided at the point is excited. Therefore, by controlling the amplification degree of the electric signal, the distance between the vibrating coil 21 and the permanent magnet 19, and the like. A larger magnetic interaction is generated, and a driving force for vibrating the vibrating coil 21 can be obtained. Because of these characteristics and being free from the acoustic restrictions described above, it is possible to provide clear hearing aid even for a highly mixed hearing loss patient.
さ らに、 本捕聴システム 1 0 は、 簡易且つ低コ ス ト な装置 であ る か ら、 今後予想さ れる高齢化社会において、 多く の 人々 に良好なコ ミ ュニケーシ ョ ンを提供する こ と ができ る。  Furthermore, since the present hearing system 10 is a simple and low-cost device, it will provide many people with good communication in the aging society expected in the future. And can be.
以上、 本発明を実施形態に基づき説明 したが、 本発明の思 想の範疇において、 当業者であれば、 各種の変更例及び修正 例に想到し得る も のであ り 、 それら変形例及び修正例につい ても本発明の範囲に属する ものと了解され、 その要旨を変更 しない範囲で種々変形可能である。 .  As described above, the present invention has been described based on the embodiments. However, various changes and modifications can be made by those skilled in the art within the scope of the concept of the present invention. It is understood that also belongs to the scope of the present invention, and various modifications can be made without changing the gist of the invention. .
また、 各実施形態は可能な限り 適宜組み合わせて実施して · も よ く 、 その場合組合わせた効果が得られる。 さ らに、 上記 実施形態には種々の段階の発明が含まれてお り 、 開示される 複数の構成要件における適宜な組合わせによ り種々の発明が 抽出され得る。 例えば、 実施形態に示される全構成要件から 幾つかの構成要件が削除されても、 発明が解決じょ う とする 課題の欄で述べた課題が解決でき、 発明の効果の欄で述べら れている効果の少なく と も 1 つが得られる場合には、 こ の構 成要件が削除された構成が発明と して抽出され得る。 Further, each embodiment may be implemented in combination as appropriate as possible, and in such a case, the combined effect can be obtained. Furthermore, the above embodiments include inventions at various stages, and various inventions can be made by appropriately combining a plurality of disclosed constituent elements. Can be extracted. For example, even if some components are deleted from all the components shown in the embodiment, the problem described in the problem to be solved by the invention can be solved, and the problem described in the effect of the invention can be solved. If at least one of the above effects can be obtained, a configuration from which this configuration requirement has been deleted can be extracted as an invention.
産業上の利用可能性 Industrial applicability
本発明によれば、 高音域であっても正確な音圧増幅特性を 実現でき 、 人体への侵襲を必要と しない補聴システム及び補 聴方法を実現する こ と ができ る。  According to the present invention, an accurate sound pressure amplification characteristic can be realized even in a high sound range, and a hearing aid system and a hearing aid method that do not require invasion of the human body can be realized.

Claims

請 求 の 範 囲 The scope of the claims
1 . 外耳領域から鼓膜にかけて設け られる補聴シス テ ムで あって、  1. A hearing aid system provided from the outer ear region to the eardrum,
入力 した外部音声に基づいて電流を発生する電流発生器と、 前記電流に基づいて、 磁場の時間的変化を誘導する第 1 の コ イ ル と 、  A current generator that generates a current based on the input external voice; a first coil that induces a temporal change in a magnetic field based on the current;
前記磁場の時間的変化に基づいて、 誘導起電力を発生する 第 2 の コ イ ルと 、  A second coil that generates an induced electromotive force based on a temporal change of the magnetic field;
前記鼓膜に対向 して設け られる磁場発生器と、  A magnetic field generator provided opposite to the eardrum,
前記第 2 の コ イ ル と電気的に接続され、 かつ前記鼓膜に設 け られる コ イ ルであ っ て、 前記誘導起電力に基づいて極性が 変化する磁場を発生し、 当該極性が変化する磁場と前記磁場 発生器が発生する磁場と の相互作用によ り 自身が振動する こ とで前記鼓膜を振動させる振動コイルと、  A coil that is electrically connected to the second coil and that is provided on the eardrum and generates a magnetic field whose polarity changes based on the induced electromotive force, and the polarity changes. A vibrating coil for vibrating the eardrum by vibrating itself by an interaction between a magnetic field and a magnetic field generated by the magnetic field generator;
を具備する補聴シス テ ム。  Hearing aid system with
2 . 前記振動コ イ ルは、 前記鼓膜の外耳領域側の面に、 ォ ィ ル又はク リ ップを用いて接着されている請求項 1記載の補 聴シス テ ム。  2. The hearing aid system according to claim 1, wherein the vibration coil is adhered to a surface of the eardrum on the side of the outer ear region using a foil or a clip.
3 . 人体との接触部分については、 生体適合性のあ.る絶縁 素材にて被覆されている請求項 1 記載の補聴システム。  3. The hearing aid system according to claim 1, wherein a contact portion with a human body is covered with a biocompatible insulating material.
4 . 前記磁場発生器は、 中耳領域寄り の外耳領域に配置さ れている請求項 1記載の補聴シス テム。 4. The hearing aid system according to claim 1, wherein the magnetic field generator is arranged in an outer ear region near a middle ear region.
5 . 前記振動コイルは、 2 O m g以下の重量である請求項 1記載の捕聴シス テ ム。  5. The listening system according to claim 1, wherein the vibration coil has a weight of 2 Omg or less.
6 . 前記振動コイルは、 円盤形である請求項 1 記載の補聴 システム。 6. The hearing aid according to claim 1, wherein the vibration coil has a disk shape. system.
7 . 前記磁場発生器と前記振動コイルと の間の距離を制御 する こ と で、 前記誘導磁場の強度を調整可能である請求項 1 記載の補聴システム。  7. The hearing aid system according to claim 1, wherein the intensity of the induced magnetic field can be adjusted by controlling a distance between the magnetic field generator and the vibration coil.
8 . 前記磁場発生器は、 永久磁石である請求項 1記載の捕 聴システム。  8. The hearing system according to claim 1, wherein the magnetic field generator is a permanent magnet.
9 . 外耳領域に設け られた音声入力手段から入力 した前記 外部音声に基づいて交流電 を発生させ、  9. Generate AC power based on the external voice input from the voice input means provided in the outer ear area,
前記交流電流を第 1 のコイルに流すこ と に よって、 磁場の 時間的変化を誘導し、  By causing the alternating current to flow through the first coil, a temporal change in the magnetic field is induced,
前記磁場の時間的変化に基づいて、 第 2 のコイルに誘導起 電力を発生させ、  Generating an induced electromotive force in the second coil based on the temporal change of the magnetic field;
前記誘導起電力に基づいて極性が変化する誘導磁場を、 鼓 膜に設け られた振動コイルに発生させ、  Generating an induced magnetic field whose polarity changes based on the induced electromotive force in a vibrating coil provided in the eardrum,
前記鼓膜に対向 して設け られた磁石によ る静磁場と、 前記 振動コイルが発生する誘導磁場によ り 、 前記振動コイルを振 動させる こ とで前記鼓膜を振動させる こ と、  Vibrating the eardrum by vibrating the vibrating coil by a static magnetic field generated by a magnet provided to face the eardrum and an induced magnetic field generated by the vibrating coil;
を具備する補聴方法。  A hearing aid method comprising:
1 0 . 前記振動コイルは、 前記鼓膜の外耳領域側の面に、 オイル又はク リ ップを用いて接着されている請求項 9記載の 補聴方法。  10. The hearing aid method according to claim 9, wherein the vibration coil is adhered to a surface of the eardrum on the side of the outer ear region using oil or a clip.
1 1 . 人体と の接触部分については、 生体適合性のある絶 縁素材にて被覆されている請求項 9記載の補聴方法。  11. The hearing aid method according to claim 9, wherein a contact portion with a human body is covered with a biocompatible insulating material.
1 2 . 前記磁石は、 中耳領域寄り の外耳領域に配置されて いる請求項 9記載の捕聴方法。 12. The listening method according to claim 9, wherein the magnet is arranged in an outer ear region near a middle ear region.
1 3 . 前記振動コ イ ルは、 2 O m g以下の重量である請求 . 項 9記載の補聴方法。 13. The hearing aid method according to claim 9, wherein the vibration coil has a weight of 2 Omg or less.
1 4 . 前記振動コ イ ルは、 円盤形である請求項 9記載の捕 聴方法。  14. The listening method according to claim 9, wherein the vibration coil has a disk shape.
1 5 . 前記磁石と前記振動コ イ ル と の間の距離を制御する こ とで、 前記誘導磁場の強度を調整可能である請求項 9記載 の補聴方法。  15. The hearing aid method according to claim 9, wherein the intensity of the induced magnetic field can be adjusted by controlling a distance between the magnet and the vibrating coil.
PCT/JP2003/002361 2002-07-24 2003-02-28 Hearing aid system and hearing aid method WO2004010733A1 (en)

Priority Applications (2)

Application Number Priority Date Filing Date Title
CA002469676A CA2469676A1 (en) 2002-07-24 2003-02-28 Hearing aid system and hearing aid method
US10/863,295 US20040234092A1 (en) 2002-07-24 2004-06-09 Hearing aid system and hearing aid method

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2002215762A JP3548805B2 (en) 2002-07-24 2002-07-24 Hearing aid system and hearing aid method
JP2002-215762 2002-07-24

Related Child Applications (1)

Application Number Title Priority Date Filing Date
US10/863,295 Continuation US20040234092A1 (en) 2002-07-24 2004-06-09 Hearing aid system and hearing aid method

Publications (1)

Publication Number Publication Date
WO2004010733A1 true WO2004010733A1 (en) 2004-01-29

Family

ID=30767939

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/JP2003/002361 WO2004010733A1 (en) 2002-07-24 2003-02-28 Hearing aid system and hearing aid method

Country Status (4)

Country Link
US (1) US20040234092A1 (en)
JP (1) JP3548805B2 (en)
CA (1) CA2469676A1 (en)
WO (1) WO2004010733A1 (en)

Cited By (28)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8396239B2 (en) 2008-06-17 2013-03-12 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US8401214B2 (en) 2009-06-18 2013-03-19 Earlens Corporation Eardrum implantable devices for hearing systems and methods
US8401212B2 (en) 2007-10-12 2013-03-19 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
US8696541B2 (en) 2004-10-12 2014-04-15 Earlens Corporation Systems and methods for photo-mechanical hearing transduction
US8715153B2 (en) 2009-06-22 2014-05-06 Earlens Corporation Optically coupled bone conduction systems and methods
US8715152B2 (en) 2008-06-17 2014-05-06 Earlens Corporation Optical electro-mechanical hearing devices with separate power and signal components
US8715154B2 (en) 2009-06-24 2014-05-06 Earlens Corporation Optically coupled cochlear actuator systems and methods
US8824715B2 (en) 2008-06-17 2014-09-02 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US8845705B2 (en) 2009-06-24 2014-09-30 Earlens Corporation Optical cochlear stimulation devices and methods
US9055379B2 (en) 2009-06-05 2015-06-09 Earlens Corporation Optically coupled acoustic middle ear implant systems and methods
US9154891B2 (en) 2005-05-03 2015-10-06 Earlens Corporation Hearing system having improved high frequency response
US9392377B2 (en) 2010-12-20 2016-07-12 Earlens Corporation Anatomically customized ear canal hearing apparatus
US9544700B2 (en) 2009-06-15 2017-01-10 Earlens Corporation Optically coupled active ossicular replacement prosthesis
US9749758B2 (en) 2008-09-22 2017-08-29 Earlens Corporation Devices and methods for hearing
US9924276B2 (en) 2014-11-26 2018-03-20 Earlens Corporation Adjustable venting for hearing instruments
US9930458B2 (en) 2014-07-14 2018-03-27 Earlens Corporation Sliding bias and peak limiting for optical hearing devices
US10034103B2 (en) 2014-03-18 2018-07-24 Earlens Corporation High fidelity and reduced feedback contact hearing apparatus and methods
US10178483B2 (en) 2015-12-30 2019-01-08 Earlens Corporation Light based hearing systems, apparatus, and methods
US10286215B2 (en) 2009-06-18 2019-05-14 Earlens Corporation Optically coupled cochlear implant systems and methods
US10292601B2 (en) 2015-10-02 2019-05-21 Earlens Corporation Wearable customized ear canal apparatus
US10492010B2 (en) 2015-12-30 2019-11-26 Earlens Corporations Damping in contact hearing systems
US10555100B2 (en) 2009-06-22 2020-02-04 Earlens Corporation Round window coupled hearing systems and methods
US11102594B2 (en) 2016-09-09 2021-08-24 Earlens Corporation Contact hearing systems, apparatus and methods
US11166114B2 (en) 2016-11-15 2021-11-02 Earlens Corporation Impression procedure
US11212626B2 (en) 2018-04-09 2021-12-28 Earlens Corporation Dynamic filter
US11350226B2 (en) 2015-12-30 2022-05-31 Earlens Corporation Charging protocol for rechargeable hearing systems
EP3831095A4 (en) * 2018-07-31 2022-06-08 Earlens Corporation Nearfield inductive coupling in a contact hearing system
US11516603B2 (en) 2018-03-07 2022-11-29 Earlens Corporation Contact hearing device and retention structure materials

Families Citing this family (9)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7421087B2 (en) * 2004-07-28 2008-09-02 Earlens Corporation Transducer for electromagnetic hearing devices
US8295523B2 (en) 2007-10-04 2012-10-23 SoundBeam LLC Energy delivery and microphone placement methods for improved comfort in an open canal hearing aid
AU2009268439B2 (en) * 2008-07-11 2013-12-05 Brain Basket, LLC Magnetostrictive auditory system
JP5219037B2 (en) * 2008-09-25 2013-06-26 国立大学法人電気通信大学 Implantable bone conduction hearing aid
US8340335B1 (en) * 2009-08-18 2012-12-25 iHear Medical, Inc. Hearing device with semipermanent canal receiver module
US9301066B2 (en) 2011-10-06 2016-03-29 Brain Basket, LLC Auditory comprehension and audibility device
CN106797522B (en) 2014-08-15 2020-08-07 智听医疗公司 In-ear hearing aid and wireless remote control using method
US9769577B2 (en) 2014-08-22 2017-09-19 iHear Medical, Inc. Hearing device and methods for wireless remote control of an appliance
US20160134742A1 (en) 2014-11-11 2016-05-12 iHear Medical, Inc. Subscription-based wireless service for a canal hearing device

Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH02119400A (en) * 1988-07-20 1990-05-07 Richards Medical Co Shield-magnet-assembly for hearing aid
JPH06501599A (en) * 1990-11-07 1994-02-17 リザウンド　コーポレイション Contact transducer assembly for hearing devices
JPH09507008A (en) * 1993-12-14 1997-07-08 フランク シー ヒル hearing aid
JPH09327098A (en) * 1996-06-03 1997-12-16 Yoshihiro Koseki Hearing aid

Family Cites Families (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4957478A (en) * 1988-10-17 1990-09-18 Maniglia Anthony J Partially implantable hearing aid device
US5259032A (en) * 1990-11-07 1993-11-02 Resound Corporation contact transducer assembly for hearing devices
DK0578752T3 (en) * 1991-04-01 1997-10-06 Resound Corp Non-conspicuous communication method using electromagnetic remote control
US6620094B2 (en) * 2001-11-21 2003-09-16 Otologics, Llc Method and apparatus for audio input to implantable hearing aids

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH02119400A (en) * 1988-07-20 1990-05-07 Richards Medical Co Shield-magnet-assembly for hearing aid
JPH06501599A (en) * 1990-11-07 1994-02-17 リザウンド　コーポレイション Contact transducer assembly for hearing devices
JPH09507008A (en) * 1993-12-14 1997-07-08 フランク シー ヒル hearing aid
JPH09327098A (en) * 1996-06-03 1997-12-16 Yoshihiro Koseki Hearing aid

Cited By (72)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9226083B2 (en) 2004-07-28 2015-12-29 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
US8696541B2 (en) 2004-10-12 2014-04-15 Earlens Corporation Systems and methods for photo-mechanical hearing transduction
US9949039B2 (en) 2005-05-03 2018-04-17 Earlens Corporation Hearing system having improved high frequency response
US9154891B2 (en) 2005-05-03 2015-10-06 Earlens Corporation Hearing system having improved high frequency response
US10154352B2 (en) 2007-10-12 2018-12-11 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
US11483665B2 (en) 2007-10-12 2022-10-25 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
US8401212B2 (en) 2007-10-12 2013-03-19 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
US10863286B2 (en) 2007-10-12 2020-12-08 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
US10516950B2 (en) 2007-10-12 2019-12-24 Earlens Corporation Multifunction system and method for integrated hearing and communication with noise cancellation and feedback management
US11310605B2 (en) 2008-06-17 2022-04-19 Earlens Corporation Optical electro-mechanical hearing devices with separate power and signal components
US10516949B2 (en) 2008-06-17 2019-12-24 Earlens Corporation Optical electro-mechanical hearing devices with separate power and signal components
US9049528B2 (en) 2008-06-17 2015-06-02 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US8396239B2 (en) 2008-06-17 2013-03-12 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US8824715B2 (en) 2008-06-17 2014-09-02 Earlens Corporation Optical electro-mechanical hearing devices with combined power and signal architectures
US8715152B2 (en) 2008-06-17 2014-05-06 Earlens Corporation Optical electro-mechanical hearing devices with separate power and signal components
US9961454B2 (en) 2008-06-17 2018-05-01 Earlens Corporation Optical electro-mechanical hearing devices with separate power and signal components
US9591409B2 (en) 2008-06-17 2017-03-07 Earlens Corporation Optical electro-mechanical hearing devices with separate power and signal components
US10516946B2 (en) 2008-09-22 2019-12-24 Earlens Corporation Devices and methods for hearing
US10743110B2 (en) 2008-09-22 2020-08-11 Earlens Corporation Devices and methods for hearing
US9749758B2 (en) 2008-09-22 2017-08-29 Earlens Corporation Devices and methods for hearing
US11057714B2 (en) 2008-09-22 2021-07-06 Earlens Corporation Devices and methods for hearing
US10511913B2 (en) 2008-09-22 2019-12-17 Earlens Corporation Devices and methods for hearing
US9949035B2 (en) 2008-09-22 2018-04-17 Earlens Corporation Transducer devices and methods for hearing
US10237663B2 (en) 2008-09-22 2019-03-19 Earlens Corporation Devices and methods for hearing
US9055379B2 (en) 2009-06-05 2015-06-09 Earlens Corporation Optically coupled acoustic middle ear implant systems and methods
US9544700B2 (en) 2009-06-15 2017-01-10 Earlens Corporation Optically coupled active ossicular replacement prosthesis
US9277335B2 (en) 2009-06-18 2016-03-01 Earlens Corporation Eardrum implantable devices for hearing systems and methods
US8787609B2 (en) 2009-06-18 2014-07-22 Earlens Corporation Eardrum implantable devices for hearing systems and methods
US10286215B2 (en) 2009-06-18 2019-05-14 Earlens Corporation Optically coupled cochlear implant systems and methods
US8401214B2 (en) 2009-06-18 2013-03-19 Earlens Corporation Eardrum implantable devices for hearing systems and methods
US10555100B2 (en) 2009-06-22 2020-02-04 Earlens Corporation Round window coupled hearing systems and methods
US11323829B2 (en) 2009-06-22 2022-05-03 Earlens Corporation Round window coupled hearing systems and methods
US8715153B2 (en) 2009-06-22 2014-05-06 Earlens Corporation Optically coupled bone conduction systems and methods
US8715154B2 (en) 2009-06-24 2014-05-06 Earlens Corporation Optically coupled cochlear actuator systems and methods
US8845705B2 (en) 2009-06-24 2014-09-30 Earlens Corporation Optical cochlear stimulation devices and methods
US8986187B2 (en) 2009-06-24 2015-03-24 Earlens Corporation Optically coupled cochlear actuator systems and methods
US9392377B2 (en) 2010-12-20 2016-07-12 Earlens Corporation Anatomically customized ear canal hearing apparatus
US11743663B2 (en) 2010-12-20 2023-08-29 Earlens Corporation Anatomically customized ear canal hearing apparatus
US10284964B2 (en) 2010-12-20 2019-05-07 Earlens Corporation Anatomically customized ear canal hearing apparatus
US10609492B2 (en) 2010-12-20 2020-03-31 Earlens Corporation Anatomically customized ear canal hearing apparatus
US11153697B2 (en) 2010-12-20 2021-10-19 Earlens Corporation Anatomically customized ear canal hearing apparatus
US11317224B2 (en) 2014-03-18 2022-04-26 Earlens Corporation High fidelity and reduced feedback contact hearing apparatus and methods
US10034103B2 (en) 2014-03-18 2018-07-24 Earlens Corporation High fidelity and reduced feedback contact hearing apparatus and methods
US9930458B2 (en) 2014-07-14 2018-03-27 Earlens Corporation Sliding bias and peak limiting for optical hearing devices
US10531206B2 (en) 2014-07-14 2020-01-07 Earlens Corporation Sliding bias and peak limiting for optical hearing devices
US11259129B2 (en) 2014-07-14 2022-02-22 Earlens Corporation Sliding bias and peak limiting for optical hearing devices
US11800303B2 (en) 2014-07-14 2023-10-24 Earlens Corporation Sliding bias and peak limiting for optical hearing devices
US10516951B2 (en) 2014-11-26 2019-12-24 Earlens Corporation Adjustable venting for hearing instruments
US9924276B2 (en) 2014-11-26 2018-03-20 Earlens Corporation Adjustable venting for hearing instruments
US11252516B2 (en) 2014-11-26 2022-02-15 Earlens Corporation Adjustable venting for hearing instruments
US10292601B2 (en) 2015-10-02 2019-05-21 Earlens Corporation Wearable customized ear canal apparatus
US11058305B2 (en) 2015-10-02 2021-07-13 Earlens Corporation Wearable customized ear canal apparatus
US11337012B2 (en) 2015-12-30 2022-05-17 Earlens Corporation Battery coating for rechargable hearing systems
US11070927B2 (en) 2015-12-30 2021-07-20 Earlens Corporation Damping in contact hearing systems
US10779094B2 (en) 2015-12-30 2020-09-15 Earlens Corporation Damping in contact hearing systems
US11350226B2 (en) 2015-12-30 2022-05-31 Earlens Corporation Charging protocol for rechargeable hearing systems
US10178483B2 (en) 2015-12-30 2019-01-08 Earlens Corporation Light based hearing systems, apparatus, and methods
US10306381B2 (en) 2015-12-30 2019-05-28 Earlens Corporation Charging protocol for rechargable hearing systems
US10492010B2 (en) 2015-12-30 2019-11-26 Earlens Corporations Damping in contact hearing systems
US11516602B2 (en) 2015-12-30 2022-11-29 Earlens Corporation Damping in contact hearing systems
US11102594B2 (en) 2016-09-09 2021-08-24 Earlens Corporation Contact hearing systems, apparatus and methods
US11540065B2 (en) 2016-09-09 2022-12-27 Earlens Corporation Contact hearing systems, apparatus and methods
US11166114B2 (en) 2016-11-15 2021-11-02 Earlens Corporation Impression procedure
US11671774B2 (en) 2016-11-15 2023-06-06 Earlens Corporation Impression procedure
US11516603B2 (en) 2018-03-07 2022-11-29 Earlens Corporation Contact hearing device and retention structure materials
US11564044B2 (en) 2018-04-09 2023-01-24 Earlens Corporation Dynamic filter
US11212626B2 (en) 2018-04-09 2021-12-28 Earlens Corporation Dynamic filter
US11606649B2 (en) 2018-07-31 2023-03-14 Earlens Corporation Inductive coupling coil structure in a contact hearing system
EP3831093A4 (en) * 2018-07-31 2022-06-15 Earlens Corporation Quality factor in a contact hearing system
US11711657B2 (en) 2018-07-31 2023-07-25 Earlens Corporation Demodulation in a contact hearing system
EP3831094A4 (en) * 2018-07-31 2022-06-15 Earlens Corporation Inductive coupling coil structure in a contact hearing system
EP3831095A4 (en) * 2018-07-31 2022-06-08 Earlens Corporation Nearfield inductive coupling in a contact hearing system

Also Published As

Publication number Publication date
JP2004064141A (en) 2004-02-26
CA2469676A1 (en) 2004-01-29
JP3548805B2 (en) 2004-07-28
US20040234092A1 (en) 2004-11-25

Similar Documents

Publication Publication Date Title
JP3548805B2 (en) Hearing aid system and hearing aid method
KR100282067B1 (en) Transducer of Middle Ear Implant Hearing Aid
US8246532B2 (en) Bone conductive devices for improving hearing
US5795287A (en) Tinnitus masker for direct drive hearing devices
KR0148085B1 (en) Headphone
KR100934273B1 (en) Vibrative type ear phone
JP4069294B2 (en) Earphone, audio transmission device
JPH11506572A (en) Implantable external auditory system with floating mass transducer
WO2015146446A1 (en) Universal speaker
JP2005175985A (en) Acoustic vibration generation device
JP2005536140A (en) Ultra-small bone-conducting speaker using a diaphragm and a mobile phone equipped with the same
US20070274551A1 (en) Implantable Bone-Vibrating Hearing Aid
JP6951491B2 (en) Bone conduction speaker
JPH09327098A (en) Hearing aid
JP3045032B2 (en) headphone
JP2006174432A (en) Bone conduction speaker, headphone, headrest, and pillow using the same
US9491551B2 (en) Network for bone conduction transducers
WO2005006809A1 (en) Piezoelectric vibration generator and vibratory sound transmitter
KR960016675B1 (en) Sound-listening device for the deaf
Hamanishi et al. A new electromagnetic hearing aid using lightweight coils to vibrate the ossicles
JP2002315098A (en) Electroacoustic transducer
JPH11104165A (en) Hearing aid
JP2004023431A (en) Speaker unit with vibration actuator
JP2012054430A (en) Bone oscillation device
Kim et al. Verification of Vibration Characteristic of Hermetically Sealed Differential Floating Mass Transducer for Implantable Middle Ear Hearing Device Using Mock-Up of Ear

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): CA US

WWE Wipo information: entry into national phase

Ref document number: 2469676

Country of ref document: CA

WWE Wipo information: entry into national phase

Ref document number: 10863295

Country of ref document: US

WWE Wipo information: entry into national phase

Ref document number: 10506962

Country of ref document: US